Electrosurgical forceps for delivering RF and/or microwave energy into biological tissue

ABSTRACT

Electrosurgical forceps in which one or more pairs of non-resonant unbalanced lossy transmission line structures are arranged on the inner surfaces of the jaws of the forceps provide both (i) active and return electrodes for a radiofrequency (RF) signal, and (ii) lossy structures for delivering a microwave signal into biological tissue in conjunction with a mechanical gripping arrangement for applying pressure to material held within the jaws. The location of the pairs of transmission lines on the jaws of the forceps and the selection of the material of the jaws is arranged to ensure that any biological tissue gripped by the jaws become the propagation medium for the RF signal and the medium into which the microwave signal is lost.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a National Stage entry of International ApplicationNo. PCT/GB2014/053834, filed Dec. 23, 2014, which claims priority toBritish Patent Application No. 1322844.0, filed Dec. 23, 2013. Thedisclosure of the prior applications are hereby incorporated in theirentirety by reference.

FIELD OF THE INVENTION

The invention relates to electrosurgical forceps for grasping biologicaltissue and for delivering microwave energy into the grasped tissue tocoagulate or cauterise or seal the tissue and/or RF energy for cuttingthe tissue. In particular, the forceps may be used to seal and/or cutblood vessels. The invention may be applied to forceps that can beinserted down the instrument channel of an endoscope or a gastroscope,or may be used in laparoscopic surgery or open surgery.

BACKGROUND TO THE INVENTION

Forceps capable of delivering heat energy into grasped biological tissueare known. For example, it is known to deliver radiofrequency (RF)energy from a bipolar electrode arrangement in the jaws of the forceps.The RF energy may be used to seal vessel by thermal denaturation ofextracellular matrix proteins within the vessel wall. The heat energymay also cauterise the grasped tissue and facilitate coagulation.

U.S. Pat. No. 6,585,735 describes an endoscopic bipolar forceps in whichthe jaws of the forceps are arranged to conduct bipolar energy throughthe tissue held therebetween.

EP 2 233 098 describes microwave forceps for sealing tissue in which thesealing surfaces of the jaws include one or more microwave antennas forradiating microwave energy into tissue grasped between the jaws of theforceps.

SUMMARY OF THE INVENTION

At its most general, the present invention provides an electrosurgicalforceps in which one or more pairs of non-resonant unbalanced lossytransmission line structures are arranged on the inner surfaces of thejaws of the forceps provide both (i) active and return electrodes for aradiofrequency (RF) signal, and (ii) lossy structures for delivering amicrowave signal into biological tissue in conjunction with a mechanicalgripping arrangement for applying pressure to material held within thejaws. The location of the pairs of transmission lines on the jaws of theforceps and the selection of the material of the jaws is arranged toensure that any biological tissue gripped by the jaws become thepropagation medium for the RF signal and the medium into which themicrowave signal is lost. The pressure applied by the mechanicalgripping arrangement may form a seal with the gripped tissue due to theresilient behaviour of the tissue and/or jaws of the forceps, which canensure that the energy is delivered controllably into the grippedtissue.

Thus, according to the invention, there is provided an electrosurgicalforceps comprising: a pair of jaw elements pivotable relative to eachother to open and close a gap therebetween; a pair of elongateconductive elements mounted in the pair of jaw elements adjacent to thegap; and a coaxial cable for conveying radiofrequency (RF) energy and/ormicrowave energy, wherein the pair of elongate conductive elements areelectrically connected to the coaxial cable and arranged to act as both(i) an active electrode and a return electrode for RF energy conveyed bythe coaxial cable, and (ii) a lossy transmission line structure formicrowave energy conveyed by the coaxial cable. Herein, the term “lossytransmission line structure” may mean a non-uniform unbalanced lossytransmission line for supporting the microwave energy as a travellingwave, the non-uniform unbalanced lossy transmission line beingnon-resonant for the microwave energy along the travelling wave. Theelongate conductive elements may have a proximal end in electricalconnection with an inner conductor or an outer conductor of the coaxialcable and a open circuit distal end. This arrangement places fewerrestrictions on the electrode configuration than in microwave forcepswhere the electrode must form a radiating antenna. Consequently, thereis more flexibility in the choice of shape of the jaw elements.

Herein the term “non-resonant” may mean that the electrical length ofthe transmission line (along the microwave energy travelling wave) isset to inhibit multiple reflections of the travelling wave, i.e. toprevent or inhibit the creation of a radiating standing wave. Inpractice this may mean that the electrical length of the transmissionline is substantially different from a multiple of a quarter wavelengthof the microwave energy (an odd or even multiple needs to be avoideddepending on whether the distal end of the transmission line is an opencircuit or a short circuit). It is particularly desirable for thetransmission line to be non-resonant when there is biological tissue inthe gap, i.e. in contact with the jaw elements. Thus, the electricallength of the transmission line may be set to avoid a multiple of aquarter wavelength of the microwave energy when the transmission line isloaded by the biological tissue in this way. Preferably the distal endof the transmission line is an open circuit, as this may enable thedevice to operate with radiofrequency (RF) energy as well as microwaveenergy.

Forming a non-resonant transmission line may prevent the device fromradiating. The microwave energy is therefore delivered into tissuethrough leakage from the transmission line structure. By setting thelength of the transmission line with knowledge of the loss level intobiological tissue at the frequency of the microwave energy, theelectrosurgical forceps of the invention can be arrange to deliversubstantially all of the power received at the proximal end of thetransmission line in a single transit of the travelling wave along thetransmission line.

In other words, the geometry of the transmission line is selected, e.g.on the basis of simulations or the like, such that it exhibits high lossin biological tissue at the frequency of the microwave energy.Similarly, the geometry of the transmission line may ensure that muchless power is lost when there is no tissue in the gap, but air instead.For example, the device may exhibit about 1 dB return loss, i.e. 80% ofpower reflected back to the generator, compared to 20% when there istissue there. Thus, four times as much power can be delivered whentissue is present in the gap. Biological tissue is lossy, i.e. it is agood absorber of microwave energy.

Preferably, the pair of jaw elements define a long-nosed forceps, e.g.where the jaws have a gharial-like appearance. For example, the lengthof the jaw elements may be more than twice, preferably more than 2.5times, their maximum width. In embodiments suitable for insertionthrough the instrument channel of an endoscope, the pair of jaw elementsmay have a length of 7 mm or more and a maximum width of 2.4 mm or less.In other embodiment, the pair of jaw elements may have a length of 10 mmor more, preferably 20 mm or more. In embodiments where the device isused laparoscopically or in open surgery, the width of the jaws may bemore than 2.4 mm, e.g. 3 mm or more. The pair of jaw elements may have acurved outer surface, e.g. to provide the forceps with a substantiallycircular transverse cross-section in order to facilitate insertionthrough the instrument channel of the endoscope. The pair of jawelements may taper away from the coaxial cable, i.e. narrow towards adistal end. This may assist the forceps to negotiate corners or curvesin the instrument channel.

The pair of jaw elements may be a continuation of the coaxial cable. Inother words, the coaxial cable may be connected to the pair of jawelements at a first end thereof, and wherein the pair of jaw elementsextend lengthwise away from the coaxial cable. As explained below, thepair of jaw element may be constrained to move with the coaxial cable,e.g. relative to some means for opening and closing the jaws. Thecoaxial cable may include a suitable bracket for securing it to the pairof jaw elements.

The pair of jaw elements may comprises a first jaw element and a secondjaw element, the first jaw element having a first inner surface thatopposes a second inner surface on the second jaw element across the gap,the first inner surface and the second inner surface extend lengthwisealong their respective jaw elements. The first inner surface and thesecond inner surface may be shaped to meet along a contact surface whenthe jaws are closed. The first inner surface and the second innersurface may have cooperating (e.g. mating) shapes. Preferably they areflat.

The inner surfaces may have a thin oblong shape. If the jaw elementstaper towards their distal ends, the inner surface may have atrapezoidal shape.

The pair of elongate conductive elements may comprise a first elongateconductive element mounted on the first inner surface and a secondelongate conductive element mounted on the second inner surface.However, in a preferred embodiment, the pair of elongate conductiveelements may comprise a first elongate conductive element mounted on thefirst inner surface and a second elongate conductive element mounted onthe first inner surface, parallel to and separated from the firstelongate conductive element. In this arrangement the spacing of the pairof elongate conductive members does not depend on the size of the gapbetween the jaw elements. The inner surface may thus deliver energy totissue in contact therewith in a consistent manner.

In a preferred embodiment, both jaw elements have a pair of elongateconductive elements on their respective inner surfaces. Thus, theforceps may include a second pair of elongate conductive elements, thesecond pair of elongate conductive elements comprising a third elongateconductive element mounted on the second inner surface and a fourthelongate conductive element mounted on the second inner surface,parallel to and separated from the third elongate conductive element.This arrangement means that energy can be delivered from both jawelements into tissue that is gripped in the gap. To achieve a consistentenergy delivery profile, the third elongate conductive element and thefourth elongate conductive element may be positioned to mirror the firstelongate conductive element and the second elongate conductive elementacross the gap. Preferably, the elongate conductive elements that faceeach other across the gap are of the same polarity.

The elongate conductive elements may comprise any suitably thinconductor. Materials with high conductivity may be desirable, e.g.silver, gold or stainless steel. For example, they may be wire or platedmetal, e.g. having a width of 0.25 mm or less. The conductive elementsmay be straight. However, in one embodiment the elongate conductiveelements may have a convoluted, e.g. meandering, distal portion. Thisstructure may reduce the reflected signal (e.g. by effectivelylengthening the conductive element). Moreover, by increasing the extentof the convolution towards the distal end, the amount of power lost overthe area of the inner surface may be made more even because there ismore transmission line in distal regions of low signal strength and lesstransmission line in proximal regions of high signal strength.

The forceps may include a spring arranged to urge the pair of jawelements into an open configuration. In embodiments where the forcepsare to be used at the distal end of an endoscope, the jaw closingmechanism is likely to be at the proximal end, whereby it is necessaryto transmit the open-close force along the length of the endoscope. Byproviding a spring, e.g. a miniature torsion spring in the pivot jointor a sprung connectors between the elongate conductive elements and thecoaxial cable, the force that needs to be transferred down the endoscopecan be reduced.

The pair of jaw elements may comprise a first jaw element and a secondjaw element that is rotatably secured to the first jaw element via apivot joint located at a proximal end of the first jaw element and thesecond jaw element. The pivot joint may be integral to the pair of jawelements. For example, the pivot joint may comprise cooperatingengagement elements formed on the first jaw element and the second jawelement. The cooperating elements may be of the cup and boss type, whererelative rotation (of the boss in the cup) is permitting, but separationof the cup and boss is restricted.

The pivot joint may include an aperture for receiving the coaxial cable,i.e. for allowing physical access to the inner surfaces of the pair ofjaw elements. The aperture may be formed from recesses or cut outs inthe pair of jaw elements, which mirror each other to form a passagethrough the jaw elements when there are interconnected.

The forceps may include a sleeve mounted over the coaxial cable and thepair of jaw elements, the sleeve being slidable relative to the pair ofjaw elements to open and close the gap. The sleeve may have an internaldiameter shaped to cause the jaw elements to close as it is drawn overthem. Sliding the sleeve relative to the coaxial cable may be performedunder the control of a jaw closing mechanism in a handle of the forceps.The jaw closing mechanism may act directly on the sleeve, or may includepull wires and push rods or the like. The sleeve may be rigid orflexible. In one embodiment the sleeve may comprise a laser-cutstainless steel tube.

In an alternative embodiment, the pivot joint may comprise a hinge pinsecured to the coaxial cable, the first jaw element and the second jawelement being pivotably mounted on the hinge pin. In this arrangement,the jaws can be opened and closed by moving them relative to the coaxialcable. Thus the forceps may include a jaw closure member secured to thefirst jaw element and the second jaw element, the jaw closure memberbeing movable relative to the coaxial cable. The jaw closure member maybe a pull rod extending alongside the coaxial cable or a pull sleevemounted around the coaxial cable.

To provide structural strength to each jaw element, the forceps mayprovide a reinforcing shell or casing on a proximal end of each of thepair of jaw elements. In a preferred embodiment, the reinforcing shellmay perform a double function. Here, the reinforcing shell may be madefrom electrically conductive material, and may be electrically connectedbetween an outer conductor of the coaxial cable and one of the pair ofelongate conductive elements. The jaw element may thus be capable oftransmitted a force, e.g. a physical pressure, on to the materialgripped between the jaw elements. The pressure applied may be enough toclose or partly close a gripped blood vessel before the application ofRF or microwave energy in order to facilitate a vessel sealingprocedure. This configuration for the jaw elements may also enable themto remain relatively cool throughout the treatment, which reduces therisk of tearing or rupturing the tissue during opening of the jaws afterthe vessel is sealed.

Herein, radiofrequency (RF) may mean a stable fixed frequency in therange 10 kHz to 300 MHz and the microwave energy may have a stable fixedfrequency in the range 300 MHz to 100 GHz. The RF energy should have afrequency high enough to prevent the energy from causing nervestimulation and low enough to prevent the energy from causing tissueblanching or unnecessary thermal margin or damage to the tissuestructure. Preferred spot frequencies for the RF energy include any oneor more of: 100 kHz, 250 kHz, 400 kHz, 500 kHz, 1 MHz, 5 MHz. Preferredspot frequencies for the microwave energy include 915 MHz, 2.45 GHz, 5.8GHz, 14.5 GHz, 24 GHz.

As mentioned above, the electrosurgical forceps of the invention may beconfigured for insertion down an instrument channel of an endoscope, ormay be arranged for use in laparoscopic surgery or in a NOTES procedureor in a general open procedure.

The forceps may include a jaw closing mechanism in mechanicalcommunication with the pair of jaw elements. For example, the jawclosing mechanism may include a handle and pull trigger in communicationwith the pair of jaw elements via one or more pull wires. In oneimplementation, the jaw closing mechanism may comprises a ratchetmechanism that permits the jaws to move between a plurality of presetseparation positions. An advantage of this is to provide control overthe pressure applied to the tissue grasped between the jaw elements. Byfixing the position of the jaw elements, the pressure may be keptsubstantially constant during treatment. Moreover, the magnitude of thepressure applied may be related to the position of the ratchet, whichmay allow easily repeatable treatment configurations to be used.

The pair of jaw elements may be rotatable, e.g. by rotating the coaxialcable or sleeve. The device may include means for rotating the jaws insitu. For example, a handle may be mounted e.g. clipped, on the coaxialcable, e.g. at a proximal end thereof. Rotation of the coaxial cableusing the handle may be transferred to the jaw elements. The handle maybe integrated with an actuator (e.g. a slider or the like) for the jawclosing mechanism.

Other aspects of the invention may include a complete electrosurgicalapparatus comprising the forceps described in communication with a jawclosure mechanism and an electrosurgical generator for delivering RFand/or microwave energy.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the invention are discussed below in detail withreference to the accompanying drawings, in which:

FIG. 1 is a schematic drawing of an electrosurgical forceps that is anembodiment of the invention;

FIG. 2 is a schematic side view of an electrosurgical forceps that is anembodiment of the invention;

FIG. 3A is a transverse cross-sectional view through the electrosurgicalforceps of FIG. 2;

FIG. 3B is a partial longitudinal cross-sectional view through theelectrosurgical forceps of FIG. 2;

FIG. 4A is a first transmission line configuration for anelectrosurgical forceps that is an embodiment of the invention;

FIG. 4B is a second transmission line configuration for anelectrosurgical forceps that is an embodiment of the invention;

FIG. 4C is a third transmission line configuration for anelectrosurgical forceps that is an embodiment of the invention;

FIG. 4D is a fourth transmission line configuration for anelectrosurgical forceps that is an embodiment of the invention;

FIG. 5A is a perspective view of a modelled structure corresponding tothe transmission line configuration of FIG. 4A;

FIG. 5B is a side view of the modelled structure of FIG. 5A showingsimulated power loss density in blood;

FIG. 5C is a transverse cross-sectional view of the modelled structureof FIG. 5A showing simulated power loss density in blood;

FIG. 6A is a perspective view of a modelled structure corresponding tothe transmission line configuration of FIG. 4C;

FIG. 6B is a side view of the modelled structure of FIG. 6A showingsimulated power loss density in blood;

FIG. 6C is a transverse cross-sectional view of the modelled structureof FIG. 6A showing simulated power loss density in blood;

FIG. 7A is a perspective view of a modelled structure corresponding tothe transmission line configuration of FIG. 4D;

FIG. 7B is a side view of the modelled structure of FIG. 7A showingsimulated power loss density in blood;

FIG. 7C is a transverse cross-sectional view of the modelled structureof FIG. 7A showing simulated power loss density in blood;

FIG. 8A is a schematic plan view of a first electrode arrangement for anelectrosurgical forceps that is an embodiment of the invention;

FIG. 8B is a schematic plan view of a second electrode arrangement foran electrosurgical forceps that is an embodiment of the invention;

FIG. 9 is a schematic partial side view of an electrosurgical forcepsthat is another embodiment of the invention;

FIG. 10 is a cross-sectional view through a jaw element that can be usedin an electrosurgical forceps that is another embodiment of theinvention;

FIG. 11 is a schematic perspective view of an electrosurgical forcepsthat is an embodiment of the invention; and

FIG. 12 is a schematic perspective view of another electrosurgicalforceps that is an embodiment of the invention.

DETAILED DESCRIPTION; FURTHER OPTIONS AND PREFERENCES

The present invention provides an electrosurgical forceps structure thatcan be operated through the channel of an endoscope. The diameter of thechannel in the endoscope may be 2.2 mm, 2.8 mm or 3.2 mm. The overallsize of the forceps may be selected accordingly.

The present invention is particularly concerned with long thin-nosedforceps comprising a pair of jaw elements with a elongate, preferablytapering, shape. For example, the jaw element may have a length of 7 mmor more, e.g. 10 mm, and possibly 20 mm, and a maximum diameter of 2.4mm. For endoscopic use, the length of the jaws may limit the ability ofthe device to be inserted along a convoluted endoscope channel. Thus,the longer length forceps may be used in other procedures, e.g.laparoscopies, or even open surgery.

The jaw elements of the electrosurgical forceps of the present inventionhave an electrode configuration that enables them to deliverradiofrequency (RF) or microwave energy into tissue that is grippedbetween them. The purpose of the forceps is to grasp (i.e. applypressure to) the tissue and to cut, coagulate or cauterise the portionheld between the forceps using the RF or microwave energy. Having longerforceps may allow longer sections of tissue to be grasped.

In order to effectively seal blood vessels, it is necessary to producehaemostasis in arteries, veins and tissue bundles. Microwave energy iseffective for this purpose, as it can create a plug or region ofcoagulation to a controllable depth (related to the square of theelectric field strength, which in turn is a function of the frequency ofthe microwave energy). A combination of RE and microwave energy may beused to create an effective seal. It is beneficial for the energydelivery to be combined with the application of pressure to the vessel,e.g. by clamping between a pair of jaw elements.

The combination of temperature elevation due to the use of RF and/ormicrowave energy and physical pressure may be particularly conducive tothe process of shrinking and denaturing collagen and other cellularproteins in an irreversible manner. The structure of collagen changes asits bonds become broken, whereby it forms a gel-like substance that actsa glue between the vessel walls. In order to transform collagen in thisway, the tissue needs to be heated between 70° C. and 95° C., which issufficient to convert collagen and elastin in the tissue to gelatin. Asthe gelatin cools while under compression, it produces an effective sealacross the lumen of the blood vessel. This seal may withstand thepressures associated with blood being pumped around the body. It followfrom this analysis that it is desirable for the jaw element to remainclamped around the blood vessel after the RF and/or microwave energyhave been applied to convert the collagen etc. to gelatin. When thefusion is complete, the vessel is plastically flexible at the seal.

One particular area of use envisaged for the invention is the removal ofpolyps, e.g. from the gastrointestinal tract, by cutting (and sealing)through the polyp's stalk. Having a longer nose may make the inventionuseful in removing polyps with wider, i.e. larger diameter, stalks.

In order to enable the device to deliver bipolar RF voltage and currentas well as microwave energy, the electrode structures on the jawelements of the forceps are transmission lines whose ends are arrangedto be an open circuit.

Given that the device will need to deliver microwave and/or RF energywhen the jaw elements are at different angles, the electrode structuresare non designed to radiate microwave energy. This contrasts withconventional microwave forceps, which seek to provide a radiatingantenna type arrangement. In the present invention, one or preferablyboth jaws of the forceps include unbalanced lossy transmission lines.

FIG. 1 shows a schematic view of an endoscopic microwave forceps 300that is an embodiment of the invention. The forceps 300 comprises a body308 having a flexible feed cable 306 extending from it. The feed cable306 is not drawn to scale; it has a length and diameter suitable forinsertion down the instrument channel of an endoscope (not shown). Thecable may be less than 2.8 mm in overall diameter to allow it to beinserted down the instrument channel of an endoscope or a gastroscope.The cable may have a length of 2 m or more. The feed cable 306 comprisesa outer sleeve that contains the coaxial cable and a jaw openingmechanism (discussed below). At a distal end of the cable 306 are a pairof jaw elements 302, 304, which are pivotable relative to each otherabout a hinge 305 to open and close a space between opposing surfacesthereof under the control of the jaw opening mechanism.

The body 308 includes a handle 310 and pull trigger 312 which operatesthe jaw closing mechanism. The pull trigger 312 may alternatively be amechanical slider or any other suitable mechanism that allow the jaws tobe opened and closed in order to apply pressure to material between theopposing surface of the jaw elements 302, 304. The body 308 is connectedby a suitable cable 314 to an electrosurgical generator (not shown)capable of generating RF and microwave energy. A suitable generator forthis purpose is described in WO 2012/076844, which is incorporatedherein by reference. This generator is arranged to measure in real timedelivered power on both a microwave channel and an RF channel (e.g. bycomparing reflected microwave power to forward microwave power and bydetecting RF voltage and current respectively). This information can beused to control an energy delivery profile in order to produce a goodseal, since the heating lowers the water content within the vessel,which in turn reduces its ability to conduct electrical current. Thechange in composition of the vessel manifests itself as a change inimpedance, which is detected in changes to the delivered power.

A pair of transmission lines 316 are formed on the inside surface of thelower jaw element 304. The transmission lines 316 may be made from wire(e.g. metal rods having a diameter of 0.25 mm or the like) or may bemetal strip lines (e.g. having a width of 0.25 mm). In this embodiment,the transmission lines 316 run parallel to each other.

The end of each of the transmission lines 316 is an open circuit. Inthis embodiment one of the transmission lines 316 is connected to theinner conductor of the coaxial cable and the other is connector to theouter conductor. The transmission lines may thus operate as eitheractive and return electrodes for an RF signal, or as a lossytransmission line for a microwave signal.

FIG. 2 shows a schematic view of an electrosurgical forceps 100 that isan embodiment of the invention. The forceps 100 comprises a pair of jawelements 102, 104 which are pivotably connected to each other at a pivotjoint 106 located at their proximal ends. Details of the pivot joint 106are discussed below with reference to FIG. 3A. Each jaw element maycomprise a body formed of a dielectric material with a low dielectricconstant, such as quartz, ceramic (e.g. alumina), PEEK, PTFE, or thelike. Having a low dielectric constant facilitate the propagation of theRF and microwave signals to the distal end of the jaw elements, evenwhen they are gripping biological tissue.

Each jaw element 102, 104 has a length of about 20 mm and a width ofless than 1.2 mm. Each jaw element 102, 104 has a smoothly curved outersurface 108 and an inner engagement surface 110. The inner engagementsurfaces 110 oppose one another such that tissue can be gripped inbetween when in use. The inner engagement surfaces 110 are flat in thisembodiment, but other surface profiles may be used.

One or both of the inner engagement surfaces 110 has an electrodeconfiguration 112 (see FIG. 3B) attached or otherwise mounted thereon.The electrode configuration is exposed such that they will make contactwith tissue in use. Further details of the electrode configurations thatcan be used in the present invention are discussed below with referenceto FIGS. 4A to 4D.

A coaxial cable 114 feeds into the proximal end of the pivot joint 106,as shown in FIG. 3A. Inside the pivot joint 106 an inner conductor andan outer conductor of the coaxial cable are connected to the electrodeconfiguration 112 (see FIG. 3B).

The coaxial cable 114 and the forceps 100 are mounted in a sleeve 116.The sleeve 116 is slidable relative to the coaxial cable and forceps 100in the direction of arrow 118 so that its can move over the proximalpart of the forceps 100 to close the jaws. The coaxial cable may besecured to a rigid bracket (see FIG. 9) so that the pivot joint cantransmit a compressing (push) force and a tensioning (pull) force on theforceps. The distal end of the coaxial cable may also be reinforced forthis purpose. The coaxial cable 114 and sleeve 116 may in turn beconnected to the relatively moving parts of the closing mechanism in thehandle of the device. This connection may be via pull rods or may bedirect.

FIG. 3A shows a cross-sectional view through the pivot joint 106. Inthis embodiment the pivot joint is a cup-boss type interface betweencooperating formations on the jaw elements 102, 104. The first jawelement 102 has a projecting boss 120 which is receiving in acooperating cup 122 formed in the second jaw element 104. The boss 120may include a retaining flange (not shown) that snap fits into acorresponding groove in the cup 122 in order to secure the joint in anaxial sense, whilst also permitting rotation.

Both the cup and the boss may include a circumferential cut out at theproximal side of the pivot joint. The cut outs cooperate to form anaperture 126 through the pivot joint 106, which can receive the distalend of the coaxial cable 114. Although not shown here, the coaxial cable114 may be secured to the inner surfaces of the pivot joint 106 by asuitable bracket (not shown) that permits rotating movement of the jawelements 102, 104 relative to the coaxial cable 114, but which transfersthe forward and backward movement of the coaxial cable 114 relative tothe sleeve 116.

A small torsion spring 124 may be mounted in the pivot joint 106. Thetorsion spring 124 may apply a torque that urges the jaw elements apart.The torque may be selected so that it is not strong enough to force thesleeve back along the coaxial cable, but rather assists the manualopening of the jaws.

FIG. 3B shows a schematic drawing of the electrical connections that aremade at the distal end of the coaxial cable 114. The inner conductor 128of the coaxial cable 114 is electrically connected to an electrodeconfiguration 112 on the inner surface of each jaw element by a firstconductive link element 130. The first conductive link element 130 maybe a short flexible wire that enables the jaws to open whilstmaintaining contact, or a metallised section of the jaw element.Alternatively, the conductive link may be a spring contact, which mayalso provides a biasing force that assists with opening the jaws.

Similarly, the outer conductor 132 of the coaxial cable 114 iselectrically connected to the electrode configuration 112 on the innersurface of each jaw element by a second conductive link element 134.Again, the second conductive link element may be a short flexible wireor a metallised section of the jaw element. However, in an alternativearrangement, the outer surface of the proximal end of both jaw elementsmay be encased in a metal shell. The metal shell may act as the secondconductive link element 134, i.e. extend round one side of the jawelement and terminate in a suitable electrode structure. In addition,the metal shell may improve the mechanical strength of the jaw elements102, 104. This structure is discussed below with reference to FIG. 10.

FIG. 4A shows a cross-sectional view of a first electrode (transmissionline) configuration 140 for an electrosurgical forceps that is anembodiment of the invention. The first electrode configuration comprisestwo wire (or microstrip) transmission lines 142, 144, with one wire oneach jaw. In this form, if the jaws are parallel, microwave transmissioncan take place along the length of the jaws. The tissue between the jawsbecomes the dielectric of the transmission line, with nearly all thepower travelling in the tissue between the jaws. The evenness of theheating will depend on the microwave properties of the tissue, i.e.relative permittivity and conductivity.

This configuration is less favoured because, for highly absorptivetissue or wide separation of the jaws, the microwave power may be nearlyall absorbed near the feed end. If the jaws are not parallel, but arerather spread towards the tip, the heating will be even moreconcentrated near the feed end.

FIG. 4B shows a cross-sectional view of a second electrode (transmissionline) configuration 146. The second electrode configuration 146comprises two wire (or microstrip) transmission lines 142, 144 formed onthe same jaw. In this form, the wires form a parallel wire transmissionline. When the jaws are closed onto tissue, one half of the transmissionline cross-section has tissue as its dielectric medium. Because of thehigh dielectric constant of the tissue, more than that proportion of thepower will travel though the tissue, and heat the tissue close to thetransmission line. Heating will take place preferentially close to thewires. The pattern of heating will be independent of how far the jawsare closed, which is advantageous when large diameter vessels (whichcause the jaw elements to be non-parallel) are treated. Because some ofthe power travels outside the tissue, the heating can extend furtheralong the jaws. If the absorption is low, some power will be reflectedfrom the open circuit end of the transmission line and cause enhancedheating near the end, and in some cases, reduced heating a shortdistance from the end, due to interference between outgoing andreflected microwave energy.

The geometry of this configuration, especially the fixed wire separationthat is independent of how far the jaws are closed, is suitable fordelivering bipolar RF energy.

An example of this geometry was simulated using CST Microwave Studio®,for a blood load 1 mm thick, with 0.25 mm diameter wires with theircentres 2 mm apart. These were fed from modelled coaxial cable (based ona Sucoform 047 cable having an outer diameter of 1.2 mm) using thesimple arrangement shown in FIG. 5A, which gave about a 5 dB returnloss.

The longitudinal heating calculated by this simulation can be seen inFIG. 5B. The heating is fairly constant in a proximal half 148 of theelectrode configuration, but towards the distal end the heating reducesand there is a null 150 caused by destructive interference due toreflection from the end.

The cross-sectional view of the simulation shown in FIG. illustratesthat the heating extends across the full depth of the blood, althoughthere is the more intense heating directly under each line and theoverall transverse profile describes a curve.

FIG. 4C shows a cross-sectional view of a third electrode (transmissionline) configuration 152. The third electrode configuration 152 comprisesfour wire transmission lines 142, 144, 154, 156, two on each jaw, withopposite polarities facing each other on the other jaw.

In this form, each jaw will behave as in shown in FIG. 4B when the jawsare far apart. There will thus be heating on both sides of the tissue,which may be advantageous. However, when the jaws are close togetherthere may be more microwave power and more heating in the region betweenthe jaws than when they are open due to the presence of the oppositepolarity wire in the other jaw. Because of this, the heating may be moreconcentrated near the feed end, particularly as at this end the jawswill be closest together in most scenarios.

The third electrode (transmission line) configuration 152 is suitablefor use with bipolar RF for the same reasons as the secondconfiguration. However, when the jaws are close together there may be anadditional path for the RF current between the jaws, which may beundesirable.

An example of this geometry was simulated using CST Microwave Studio®,for a blood load 1 mm thick, with 0.25 mm diameter wires with theircentres 2 mm apart (i.e. 1.75 mm between the outer edges of the wires).These were fed from modelled coaxial cable (based on a Sucoform 047cable having an outer diameter of 1.2 mm) using the simple arrangementshown in FIG. 6A, which gave about a 5 dB return loss.

The longitudinal heating calculated by this simulation can be seen inFIG. 6B. Similarly to FIG. 5B the heating is fairly constant for theproximal half 148 of the electrode configuration. However, towards thedistal end the heating reduces and there is a null 150 caused bydestructive interference due to reflection from the end.

The heating profile across the full depth of the blood is shown in FIG.6C. There are two bands of heating 158, 160 between the opposite jaws,with a cool gap 162 between. Heating is mainly between wires on oppositejaws, not between wires on the same jaw.

FIG. 4D shows a cross-sectional view of a fourth (and most preferred)electrode (transmission line) configuration 164. The fourth electrodeconfiguration 164 comprises four wire transmission lines 142, 144, 154,156, two on each jaw, with same polarities facing each other on theother jaw.

In this form, each jaw will behave as shown in FIG. 4B when the jaws arefar apart and when the jaws are close together. Heating will be fromboth jaws.

The fourth electrode (transmission line) configuration 152 is suitablefor use with bipolar RF for the same reasons as the secondconfiguration. When the jaws are close together the paths for RF currentremain similar, which ensures consistent behaviour while the jaws are inthe process of being closed.

An example of this geometry was simulated using CST Microwave Studio®,for a blood load 1 mm thick, with 0.25 mm diameter wires with theircentres 2 mm apart (i.e. a physical separation of 1.75 mm between theconductors). These were fed from modelled coaxial cable (based on aSucoform 047 cable having an outer diameter of 1.2 mm) using the simplearrangement shown in FIG. 7A, which gave about a 5 dB return loss.

The longitudinal heating calculated by this simulation can be seen inFIG. 7B. Similarly to FIG. 5B the heating is fairly constant for theproximal half 148 of the electrode configuration. Towards the end distalthe heating reduces and there is a null 150 caused by destructiveinterference due to reflection from the end.

The heating profile across the full depth of the blood is shown in FIG.7C. There is one wide band 166 of heating, between the four wires.

FIG. 8A shows a plan view of an inner surface 170 of a jaw element 172.A pair of conductive strips 174, e.g. made of wire or a deposited stripof metal, provide the electrode configuration mentioned above. Theconductive strips 174 are straight and parallel. As mentioned above, oneside effect of this arrangement is a null in the delivered microwaveenergy at around three quarters of the way toward the distal end of thejaw element 172. FIG. 8B shows a plan view of an inner surface 170 of ajaw element 172 in which a pair of parallel conductive strips 176 have adistal portion that is convoluted instead of straight in order to reduceor minimize the null effect. The convoluted path effectively increasesthe length of the transmission lines in a manner that reduces thereflections from the distal end and therefore reduces the magnitude ofthe null.

FIG. 9 is a schematic drawing showing a view of connection interfacebetween a coaxial cable and jaw element in an electrosurgical forceps200 that is another embodiment of the invention. In this embodiment, thejaw element is a three piece construction comprises a metal shell 204, asupport body 206, e.g. of rigid plastic, and a dielectric base 208, e.g.of ceramic, for supporting the active electrode. The lower jaw elementand the support body and dielectric base of the upper jaw element areomitted from FIG. 9 for clarity. In another embodiment, the jaw elementmay be formed from a stainless steel body, with portions of goldmetallisation formed thereon to provide the first and second conductiveelements. In this arrangement, the jaw elements may be electricallyisolated from each other by formed the pivot mechanism from aninsulating material such as ceramic. For example, if a hinge is used,the hinge pin may be formed from ceramic and one or more ceramic shimsmay be located between surfaces of the jaws that may slide past oneanother.

FIG. 10 shows a cross-sectional view through the three pieces of the jawelement 201. It can be seen that the inner surface 207 of the jawelement 201 has two conductive wires 210, 212. The first conductive wire210 is mounted on the dielectric base 208, which isolates it from thesecond conductive wire 212 and supports propagation of RF and microwaveenergy. The second conductive wire 212 is part of the metal shell 204.The support body 206 is effectively an electrically insulating fillbetween the metal shell 204 and the dielectric base 208. The outersurfaces of the metal shell 204 and support body 206 are shaped to givethe jaw element a smooth outward appearance.

Each jaw element has its own respective metal shell 204. The metalshells 204 are pivotable relative to each other about a hinge element214. The hinge element 214 comprises a pair of hinge bars 216 secured tothe distal end of the coaxial cable 202, and a pair of inwardlyprojecting stubs which mate with corresponding slots 220 on the metalshells 204. In use, the coaxial cable may be pulled or pushed relativeto a surrounding sleeve (not shown) to cause the metal shells 204 topivot about the hinge and thereby open and

The hinge element 214 may be made of conductive material, and may alsoact as a conductive link between the outer conductor 222 of the coaxialcable 202 and the metal shell 204. The inner conductor 224 of thecoaxial cable 202 may be connected to the first conductive wire 210 by aseparately conductive link element (not shown), such as a short flexiblewire made of silver, gold or any other highly conductive material.

FIG. 11 shows a schematic view of one example of a jaw configurationthat could be used in an electrosurgical forceps 400 that is anembodiment of the invention. The forceps 400 comprise a pair of jawelements 402, 404 hinged to the distal end of a sleeve 406. The sleeve406 carries a coaxial cable (not shown) for conveying RF and/ormicrowave energy to the jaw elements, and a jaw opening mechanism. Inthis embodiment, the jaw opening mechanism comprises a pair of flexiblepush rods 408 that extend through the sleeve and protrude at the distalend. Each push rod is attached to the underside of a respective jawelement. The jaw elements 402, 404 may thus be opened and closed byextending and retracting the push rods 408.

FIG. 12 shows a schematic view of a pantograph-type jaw configurationthat could be used in an electrosurgical forceps 450 that is anembodiment of the invention. The forceps 450 comprise a pair of jawelements 402, 404, which are each pivotably mounted on a extensionelement 410, which in turn is hinged on the distal end of a sleeve 406.The sleeve 406 carries a coaxial cable (not shown) for conveying RFand/or microwave energy to the jaw elements, and a jaw openingmechanism. In this embodiment, the jaw opening mechanism comprises apush rod 412 that extends through the sleeve and protrudes at its distalend. The push rod 412 has a pair of rigid, fixed length connector rods414 pivotably attached at its distal end. Each connector rod 414 isattached to the underside of a respective jaw element. The jaw elements402, 404 may thus be opened and closed by extending and retracting thepush rod 412, which causes the connector rods to force apart the jawelements 402, 404.

In the embodiment shown in FIG. 12, the jaw elements may remainsubstantially parallel during opening and closing.

The forceps may be used in a method of vessel sealing that comprisesthree stages:

(1) applying pressure to the vessel (e.g. polyp stalk) by clamping itbetween the jaw elements to bring opposing side walls of the vesselcloser to one another,

(2) applying RF energy and/or microwave energy to the compressed tissuein order to heat the collagen therein and make it mobile throughdenaturation,

(3) allow the collagen to cool while maintaining the pressure to sealthe vessel.

The invention claimed is:
 1. Electrosurgical forceps comprising: a pairof jaw elements that are pivotable relative to each other to open andclose a gap therebetween, the pair of jaw elements comprising a firstjaw element and a second jaw element that is rotatably secured to thefirst jaw element via a pivot joint located at a proximal end of thefirst jaw element and the second jaw element; a pair of elongateconductive elements, wherein each jaw element has a respective one ofthe pair of elongate conductive elements mounted therein adjacent to thegap; and a coaxial cable for conveying radiofrequency (RF) energy and/ormicrowave energy, wherein the pivot joint includes an aperture forreceiving the coaxial cable, and wherein the pair of elongate conductiveelements are electrically connected to the coaxial cable and arranged toact as both (i) an active electrode and a return electrode for RF energyconveyed by the coaxial cable, and (ii) a non-uniform unbalanced lossytransmission line to support the microwave energy as a travelling wave,the non-uniform unbalanced lossy transmission line being non-resonantfor the microwave energy along the travelling wave.
 2. Electrosurgicalforceps according to claim 1, wherein the pair of jaw elements have alength of 5 mm or more and a maximum width of 2.4 mm or less. 3.Electrosurgical forceps according to claim 1, wherein the pair of jawelements have a curved outer surface that tapers away from the coaxialcable.
 4. Electrosurgical forceps according to claim 1, wherein thecoaxial cable is connected to the pair of jaw elements at a first endthereof, and wherein the pair of jaw elements extend lengthwise awayfrom the coaxial cable.
 5. Electrosurgical forceps according to claim 4,wherein the first jaw element has a first inner surface that opposes asecond inner surface on the second jaw element across the gap, the firstinner surface and the second inner surface extending lengthwise alongtheir respective jaw elements.
 6. Electrosurgical forceps according toclaim 5, wherein a first elongate conductive element of the pair ofelongate conductive elements is mounted on the first inner surface and asecond elongate conductive element of the pair of elongate conductiveelements is mounted on the second inner surface.
 7. Electrosurgicalforceps according to claim 1, wherein the elongate conductive elementscomprise wire or plated metal having a width of 0.25 mm or less. 8.Electrosurgical forceps according to claim 1 including a spring arrangedto urge the pair of jaw elements into an open configuration. 9.Electrosurgical forceps according to claim 1, wherein the pivot jointcomprises cooperating engagement elements formed on the first jawelement and the second jaw element.
 10. Electrosurgical forcepsaccording to claim 1 including a sleeve mounted over the coaxial cableand the pair of jaw elements, the sleeve being slidable relative to thepair of jaw elements to open and close the gap.
 11. Electrosurgicalforceps according to claim 1, wherein the pivot joint comprises a hingepin secured to the coaxial cable, the first jaw element and the secondjaw element being pivotably mounted on the hinge pin. 12.Electrosurgical forceps according to claim 11 including a jaw closuremember secured to the first jaw element and the second jaw element, thejaw closure member being movable relative to the coaxial cable. 13.Electrosurgical forceps according to claim 12, wherein the jaw closuremember is a pull rod extending alongside the coaxial cable or a pullsleeve mounted around the coaxial cable.
 14. Electrosurgical forcepsaccording to claim 12 including a ratchet mechanism connected to the jawclosure member to permit relative movement of the jaw elements between aplurality of preset separation positions.
 15. Electrosurgical forcepsaccording to claim 1, wherein the elongate conductive elements have aconvoluted distal portion.
 16. Electrosurgical forceps according toclaim 1, wherein each jaw element in the pair of jaw elements has areinforcing shell at its proximal end.
 17. Electrosurgical forcepsaccording to claim 16, wherein the reinforcing shell is made fromelectrically conductive material, and is electrically connected betweenan outer conductor of the coaxial cable and one of the pair of elongateconductive elements.
 18. Electrosurgical forceps according to claim 16,wherein the jaw elements are configured to transmit a compression forceto tissue grasped therebetween.
 19. Electrosurgical forceps comprising:a pair of jaw elements that are pivotable relative to each other to openand close a gap therebetween, the pair of jaw elements comprising afirst jaw element and a second jaw element that is rotatably secured tothe first jaw element via a pivot joint located at a proximal end of thefirst jaw element and the second jaw element, wherein the first jawelement has a first inner surface that opposes a second inner surface onthe second jaw element across the gap, the first inner surface and thesecond inner surface extending lengthwise along their respective jawelements; a pair of elongate conductive elements, wherein the pair ofelongate conductive elements comprises a first elongate conductiveelement mounted on the first inner surface and a-second elongateconductive element mounted on the first inner surface, parallel to andseparated from the first elongate conductive element; and a coaxialcable for conveying radiofrequency (RF) energy and/or microwave energy,wherein the pivot joint includes an aperture for receiving the coaxialcable, and wherein the pair of elongate conductive elements areelectrically connected to the coaxial cable and arranged to act as both(i) an active electrode and a return electrode for RF energy conveyed bythe coaxial cable, and (ii) a non-uniform unbalanced lossy transmissionline to support the microwave energy as a travelling wave, thenon-uniform unbalanced lossy transmission line being non-resonant forthe microwave energy along the travelling wave.
 20. Electrosurgicalforceps according to claim 19 including a second pair of elongateconductive elements, the second pair of elongate conductive elementscomprising a third elongate conductive element mounted on the secondinner surface and a fourth elongate conductive element mounted on thesecond inner surface, parallel to and separated from the third elongateconductive element.
 21. Electrosurgical forceps according to claim 20,wherein the third elongate conductive element and the fourth elongateconductive element are positioned to mirror the first elongateconductive element and the second elongate conductive element. 22.Electrosurgical forceps according to claim 21, wherein the elongateconductive elements that face each other across the gap are of oppositepolarities.
 23. Electrosurgical forceps according to claim 21, whereinthe elongate conductive elements that face each other across the gap areof the same polarity, and wherein the elongate conductive elementslocated on the same inner surface are of opposite polarity.